Breathing assistance device

ABSTRACT

The present invention proposes a breathing assistance device for a patient, comprising:
         A source of respiratory pressurised gas,   A breathing connection to allow the patient to receive said gas,   At least one sensor for acquiring a parameter representative of the operation of the device,   characterised in that said gas source is a ventilator, and said ventilator is integrated into a removable module which also comprises at least one sensor for acquiring a parameter representative of the operation of the device.

CROSS-REFERENCE TO RELATED APPLICATIONS

This application is a continuation of U.S. application Ser. No.10/563,493, filed on Jan. 4, 2006, which is a national phase entry under35 U.S.C. §371 of International Application No. PCT/IB2004/002440, filedJul. 5, 2004, which claims priority from French Application No. 0308187,filed on Jul. 4, 2003, and of U.S. Provisional Patent Application No.60/495,922, filed on Aug. 18, 2003, all of which are incorporated hereinby reference.

BACKGROUND OF THE INVENTION

The present invention generally relates to breathing assistance devices.

More precisely, the invention concerns a breathing assistance device fora patient, comprising:

a source of respiratory pressurized gas,

a breathing connection to allow the patient to receive said gas,

at least one sensor for acquiring a parameter representative of theoperation of the device.

Devices of this type are already known.

FIG. 1 therefore diagrammatically illustrates an example 10 of a knowndevice.

The device 10 comprises a fixed console 100.

This fixed console 100 comprises among others a source of pressurizedgas 105.

In practice, this gas source can be in the form of a ventilator or a fan(the term ventilator is retained in the text hereinbelow forconvenience).

The ventilator is mounted fixed inside the console.

The fixed console 100 also generally comprises a central unit forcontrolling the operation of the device.

Such a central unit is connected to one or more sensors of parameter(s)representative of the operation of the device (typically the gas flowrate and the gas pressure), and it controls the operation of the deviceas a function of this/these parameter(s).

The console comprises means for interfacing with a user (who can be thepatient himself).

These means are illustrated schematically here in the form of a screen101 and control/adjustment buttons 102.

The respiratory gas is conveyed from the source 195 to the patient via aconduit 110, whereof a first end is connected to said source.

The second end of the conduit 110 will be generally designated in thistext by the term “breathing connection”.

More generally still, a <<breathing connection>> designates in this textthe interface between the device and the patient.

Such a <<breathing connection>> can correspond to a breathing mask, asillustrated in the illustration in FIG. 1.

It is specified that it is also envisageable to utilize a device of thistype in so-called <<intrusive>> mode, where the patient is thenintubated with this second end.

In this latter case, the <<breathing connection>> corresponds simply tothe end of the conduit with which the patient is intubated.

In the example illustrated in FIG. 1, the mask 120 comprises vents 121for arranging leaks of respiratory gas. These leaks especially allow apart of the CO2 rejected by the patient to be evacuated duringexpiration phases.

The elements described hereinabove in reference to FIG. 1 are found in alarge number of known devices.

These devices provide substantial assistance.

They are nonetheless associated with certain disadvantages, and certainlimitations. Certain of these disadvantages/limitations will beexplained hereinbelow.

First of all, the general configuration of such devices generally leadsto fairly significant space requirements (due to the presence of thefixed console, the conduit connecting the console and the patient,possibly other conduits such as an expiration conduit).

This space requirement can constitute a disadvantage per se.

In addition, this general configuration also gives rise to constraintsfor the patient.

In particular, the patient must remain attached to the fixed console, byway of the conduit.

This naturally limits the movements of the patient, and can constitutean inconvenience (especially at night, within the scope for example ofsleep apnoea treatment).

Furthermore, in such a general configuration, even if a certainproportion of the CO₂ expirated by the patient can escape via the ventsof the mask, the remaining proportion of CO₂ is <<trapped>> in theconduit, where it is forced back during expiration.

A <<plug>> of CO₂ is thus formed in the conduit. And pollutants such asfor example germs expirated by the patient can be found in this<<plug>>.

This plug of CO₂ can thus constitute pollution for the patient, who canpossibly be induced to inspire a part of the CO2 and germs expiratedpreviously.

This plug of CO₂ can also constitute pollution for the device, where itis capable of migrating or being pushed towards elements of the devicesuch as the gas source located at the end of the conduit 110.

The presence of CO₂ and its possible pollutants in such elements of thedevice can even constitute a danger for the patient.

In fact, in the case where CO₂ and/or pollutants would be present insuch elements of the device, the device would risk conveying this CO₂and/or these pollutants to the patient.

This can constitute a danger for the patient (especially in the case ofhypercapnic patients).

It is thus necessary in this case to proceed with disassembling andcleaning these elements. This constitutes a fastidious operation, whichalso makes the device unavailable.

It will also be noted that even by abstracting the specific problem ofpollution which has just been explained a propos CO₂ trapped in aconduit, patients are exposed to the disadvantages associated withcleaning operations mentioned hereinabove.

Therefore, the known devices are exposed to these disadvantages, whichare considered particular causes of pollution (associated or not withthe conduit), or not.

It is thus necessary from time to time to proceed with disassembling andcleaning the ventilator, which, as explained, constitutes a fastidiousoperation, and which also has the disadvantage of making the deviceunavailable.

With respect to the aspects associated specifically with the generalconfiguration comprising a console and a conduit, it is also to be notedthat the presence of the conduit causes losses of charge and pneumaticinertia:

which diminish the energetic yield of the device,

and which increase the complexity of the control of the device, wherethese losses of charge and inertia must be integrated into the controlprograms of the device.

This disadvantage is naturally all the more sensitive than the conduitis long.

Furthermore, limitations and disadvantages are associated specificallywith the presence of the mask vents.

And in certain applications (especially in the case of a devicefunctioning in BPAP or CPAP mode), the known devices generally utilizedtake on the configuration illustrated FIG. 1, which comprises a maskwith vents.

It is specified that the CPAP type (acronym of the English termContinuous Positive Airway Pressure—this type also able to be designatedin French by the acronym PPC for Pression Positive Continue [ContinuousPositive Pressure]) designates the devices at a single pressure level.

In these devices, the speed of rotation of the ventilator is regulatedby measuring the pressure exerted on the single conduit of the device(conduit 110 in FIG. 1).

The unique control pressure is generally fixed at a value less than 20mbars (this value is expressed in surpressure relative to atmosphericpressure), which limits the use of such devices to the treatment oflight pathologies.

The devices of BPAP type (acronym of the English term Bilevel PositiveAirway Pressure, this acronym being a registered trademark—and this typealso able to be designated in French by the acronym VNDP for VentilationNasale a Deux niveaux de Pression [Nasal Ventilation at two PressureLevels]) has the same general architecture, but functions with twocontrol pressures (a value of inspiration pressure and a value ofexpiration pressure).

The devices mentioned hereinabove referring to FIG. 1 (in particularoperating in BPAP or CPAP mode) therefore often comprise masks withvents.

Such a mask with vents can cause unwanted effects.

In particular, the gas outlets associated to the vents can be directedtowards parts of the body of the patient, and cause phenomena such asdesiccation of these parts of the body.

This is a disadvantage, especially when such consequences are observedin the eyes of the patient.

In addition, leaks must be taken into consideration for administeringthe operation of the device (for example consideration of these leaks inthe programs of the central unit which administers this operation).

This naturally tends to increase the complexity of the device.

It thus appears that certain disadvantages and limitations are linked tothe known devices described hereinabove.

SUMMARY OF THE TECHNOLOGY

The aim of the invention is to eliminate these disadvantages.

In order to attain this goal, the invention proposes a breathingassistance device for a patient, comprising:

a source of respiratory pressurised gas,

a breathing connection to allow the patient to receive said gas,

at least one sensor for acquiring a parameter representative of theoperation of the device,

characterised in that said gas source is a ventilator, and saidventilator is integrated into a removable module which also comprises atleast one sensor for acquiring a parameter representative of theoperation of the device.

Preferred but non-limiting aspects of such a device are the following:

said module comprises a respiratory gas pressure sensor and a flowsensor,

the module is fixed on the device by a removable connection, such thatdisassembly of the module is made easier,

said removable connection comprises a thread pitch,

said removable connection comprises means for clipping the module,

said breathing connection is made in the form of a mask,

said mask is a mask without means enabling leaks, such as vents,

the module is fixed directly on the breathing connection, such that thedevice does not comprise a conduit for conveying respiratory gas whichwould connect the breathing connection to a fixed offline console of thedevice,

the ensemble formed by the breathing connection and the module is linkedto a control console of the device,

said link permits transmission between said ensemble and said dataconsole,

said link is a wireless link,

said link enables the energy required for operating the components ofthe module to be conveyed from said console to said ensemble,

said link is a wire link,

the ventilator is an axial ventilator,

the rotor of the ventilator axial comprises a single stage,

in the ventilator the respective directions of the input and the outputof respiratory gas are substantially parallel,

the ventilator comprises:

-   -   a central input substantially aligned with the axis of rotation        of the rotor of the ventilator,    -   an outlet allowing the flux generated by said rotor to be        collected according to an oblique direction relative to said        axis of rotation, and    -   means for rectifying said flux generated and collected, so that        this flux flows out of the ventilator in a general direction        substantially parallel to said axis of rotation of the rotor of        the ventilator,

the device is of type BPAP,

the device is of type CPAP.

A number of devices or systems have been proposed for assisting patientsto breathe—as an example one can refer to FR 2 784 587, WO 03/049793 andDE 101 16 361—but such devices do not disclose or even suggest thespecific features of the invention (to begin with a ventilator arrangedinto a removable module).

BRIEF DESCRIPTION OF THE DRAWINGS

Other aspects, aims and advantages will emerge better from reading thefollowing description of the invention, made in reference to theattached diagrams.

FIG. 1 has already been made in reference to the prior art;

FIG. 2 is a diagrammatic illustration of a module put to use in a deviceaccording to the present invention;

FIG. 3 a is a diagrammatic illustration of a ventilator which can beused in a module according to the present invention, this ventilatorbeing illustrated according to a longitudinal section;

FIG. 3 b is a diagrammatic illustration of another ventilator which canbe used in a module according to the present invention, this ventilatorbeing illustrated according to a longitudinal section;

FIGS. 4 a and 4 b are a diagrammatic illustration of two variants ofutilizing the invention; and

FIG. 5 is a diagrammatic illustration of a console which can be utilizedin another variant of the invention.

FURTHER DESCRIPTION OF THE TECHNOLOGY

FIG. 2 diagrammatically illustrates a module 20.

This module has the general form of a cylinder with a circular base.

The diameter of this cylinder can for example be of the order of 25 to35 mm.

The module 20 comprises two main parts:

a first part 21, which contains a ventilator,

a second part 22, which contains one or more sensors for acquiringparameter(s) representative of the operation of the ventilator and ofthe flux of respiratory gas generated by this ventilator.

The module 20 is fitted with removable fixing means, for cooperatingwith complementary means of the device.

The module 20 is in effect intended to be able to be mounted anddismounted in a removable and simple manner on the device according tothe present invention.

And, as will be seen, this module 20 can be implanted into differentplaces in the device, according to embodiments of the invention.

The part 21 thus contains a ventilator, which is capable of generating aflux of respiratory pressurised gas.

To increase the compactness of the module 20, and permit dimensions ofthe order of those mentioned hereinabove (25 to 35 mm in diameter), theventilator must have a specific configuration.

More precisely, this ventilator is an axial ventilator (which signifiesthat the air exits this ventilator in a direction substantially parallelto the axis of rotation of the revolving elements of the ventilator).

The applicant has in fact determined that this type of ventilator hadless space requirement than a ventilator of centrifugal ventilator type,in which the gas exits in a direction tangential to the rotation disk ofthe rotor of the ventilator.

In particular, the embodiment of such a ventilator would requireproviding around the rotor a collection and rectification channel of theflux which would substantially increase the diameter of the module.

FIG. 3 a thus diagrammatically illustrates an embodiment of the axialventilator contained in the part 21 of the module.

This figure diagrammatically illustrates a ventilator 210, provided witha rotor 211 capable of revolving about an axis of rotation 2110.

The rotor is driven by a motor integrated into the ventilator (motor notshown for the sake of clarity).

It is specified that the rotor can be a single-stage rotor (that is,comprising only a single series of blades), or a two-stage rotor (thatis, comprising two series of blades mounted behind the other on the axisof rotation).

An air inlet 212 is provided, opposite the centre of the rotor 211. Thisair inlet is axial (it introduces the air aspirated by rotation of therotor in a direction parallel to that of the axis of rotation 2110).

The air is expelled from the ventilator via an outlet 213 (which is hereshown in section in the form of two conduits, and which can have ageometry of revolution around the axis of rotation 2110).

It will be noted that the section of the outlet 213 comprises two mainparts:

a first part 2131 which is immediately adjacent to the rotor. This part2131 is oriented obliquely relative to the axis 2110, so as to collectwith maximum efficiency the flux of gas pushed by the rotor—the speed ofthis flux not only has an axial component (parallel to the axis 2110),but also a tangential component,

a second part 2132, which is downstream of the first part 2131 and whichis oriented substantially parallel to the axis 2110, such as to rectifythe flux originating from the ventilator in the axial direction of thisventilator.

Arranging the two parts 2131 and 2132 is done such as to minimize thespace requirement of the ventilator, and especially so as to conserve areduced diameter for this ventilator.

The second part 22 of the module 20 comprises at least one sensor foracquiring a parameter representative of the operation of the device.

More precisely, in a preferred embodiment of the invention this part 22comprises at least one pressure sensor and one flow sensor.

FIG. 3 b represents another possible configuration for an axialventilator 210′ contained in the part 21 of the module.

This ventilator comprises an inlet rotor 2110′, moved in rotation by amotor M.

The motor M can also move in rotation another rotor 2111′, located atthe outlet of the ventilator.

Redressing means 213′ can be provided immediately downstream of theinlet rotor.

At least one sensor for acquiring a parameter representative of theoperation of the device is located in the part of the ventilator whichis downstream of the inlet rotor (and of the redressing means if thereare any).

More precisely, in a preferred embodiment of the invention this partcomprises at least one pressure sensor and one flow sensor.

The module 22 also comprises means for amplifying and digitizing signalsoriginating from the sensors of the part 22 (or of the part 21 if thesensors are located into this part), and a means of exchanging thesesignals with an offline console of the device.

This offline console can be a fixed console as in the prior art.

This console can also be a removable console, in the form of a device ofreduced size.

FIG. 4 a illustrates a first variant embodiment of the invention.

In this figure, a patient P is shown breathing via a mask 420.

This mask 420 corresponds to the <<breathing connection>> which has beenmentioned in the introduction to this text, and which allows the patientto breathe the gas coming from a source of pressurized gas.

In the different variant embodiments of the invention, it is in factgenerally preferred to have the breathing connection made in the form ofa mask (and as will be seen more precisely, a mask without vents).

Nevertheless it is specified that all the variant embodiments of theinvention which are put forward in this text can be realized with abreathing connection which does not correspond to a mask, but to an endof a conduit or a portion of conduit allowing the patient to beintubated.

With respect to FIG. 4 a, it is noticed that the mask 420 is notprovided with any opening allowing leaks, such as vents.

The mask 420 is thus adapted to allow practically no gas leak.

And it should be further noticed that the breathing connection is notassociated to any expiratory valve (also sometimes referred to as“exhalation valve”).

This configuration without leakage means such as vents in a mask or anexpiration valve allows:

to make the design, the construction and the operation of the devicesimple,

to maximally benefit from the proximal effect associated with aventilator arranged in the vicinity of the mask, which prevents theformation of a CO2 plug.

In this respect, the invention is totally different from devices such asthe one disclosed by EP 164 946:

it should first be noted that the device of EP 164 946 belongs to quitea different category of devices—it is a device which is merely designedfor filtering the air inspired by a user and there is no arrangement forventilating a patient according to different modes (in particular it isof course not possible in the case of the device of EP 164 946 tocontrol the operation selectively in a barometric mode, or in avolumetric mode),

this difference with the very nature of the device of EP 164 946 isfurther illustrated by the fact that the compressor of this device isconsidered as an element that is not even worth cleaning—rather, it ismerely replaced when necessary,

the device of EP 164 946 is arranged with an expiratory valve 8—which isperfectly understandable since in this filtering device it is desired toavoid breathing out through the filter. In this respect the presentinvention provides a device for which it is possible to breathe outdirectly through the turbine (in the versions of the invention where theturbine is in the direct vicinity of the mask so that there is noinspiration duct).

A module 20 of the type described in reference to FIG. 2 is connected tothe mask 420.

More precisely, the module 20 is fixed in a removable manner on the maskby removable fastening means such as for example means comprising athread pitch, or clipping means.

It is specified that generally any removable fastening means can beadopted to ensure fixing of the module onto the mask 420 (and moregenerally onto any part of the device intended to receive the module).

The module 20 is fixed onto the mask 420 such that the ventilator ofthis module feeds the internal space of the mask with respiratory gas.

FIG. 4 a also illustrates an offline console 400.

This console comprises interface means such as a screen and controlbuttons, as the console 100 of FIG. 1.

It will be noted all the same that in the case of the device in FIG. 4a, no ventilator or source of pressurized gas is connected to theconsole.

In effect, in this case the ventilator is directly connected to the mask420.

The console 400 may integrate a central control unit for operating thedevice.

In this case, this control unit receives the signals originating fromthe sensors of the module 20.

To this end, the signals have previously been amplified and digitised inthe module, by the means mentioned hereinabove.

Transmission of signals between the module 20 and the central unit ofthe console 400 is made in the case of the device of FIG. 4 a by a linkof wire type.

In this case, a data transmission cable 430 assures transmission of thesignals from the module to the central unit.

As a function of the value of these signals, the central unit works outa control value of the speed of rotation destined for the ventilator.

This control value can in particular be a value of the speed of rotationof the rotor of the ventilator.

This order is transmitted to the ventilator via the same link betweenthe console and the module (in the case of the device in FIG. 4 a, thecable 430).

It is understood that the device in FIG. 4 a offers numerous advantages.

In particular, it is noted that no conduit connect the console 400 andthe patient to draw off the respiratory gas to said patient.

This offers considerable comfort and extensive flexibility in use.

In addition, the absence of conduit effectively eliminates thedisadvantages mentioned in the introduction to this text with referenceto plugs of CO2 which can be created in the conduits of the knowndevices.

This is an important advantage, which can be referred to as the“proximal effect”.

And more generally (and abstracting the considerations associated withthe presence or not of a conduit), the fact that the module is removableallows the ventilator to be disassembled rapidly and simply, in order toproceed with cleaning it, if required.

Furthermore, since the mask is provided without vents, in the case ofthe invention there is no exposure to the disadvantages associated withthe presence of such vents.

It will also be noted that the fact that the ventilator and itsassociated sensors are placed closer to the patient allows parameterswhich are actually representative of the state of the gas in thevicinity of the patient to be transmitted to the central unitcontrolling the operation of the device.

It is specified in this regard that implantation of the module in themask is done so as to let only a small volume inside the mask.

Operation of the device can thus be tracked by the central unit in<<truly>> real time, with a response time which is extremely lowrelative to the status changes of the device.

In particular, the fact of being free of the length of the conduitconventionally conveying the gas to the patient allows the operation ofthe device to be tracked closely: the effect of the commands transmittedto the ventilator will have immediate repercussions on the patient.

Another advantage holds that the motor of the ventilator is in theimmediate vicinity of the sensors of the part 22 of the module 20.

The heat released by this motor in effect reheats the respiratory gaspassing into these sensors, which effectively prevents the condensationof gas near these sensors.

It will be noted that the patient can use a remote control to controlthe operation of the console 400 from a distance.

Furthermore, the console 400 can itself be reduced to a simple remotecontrol allowing the operation of the device to be controlled.

FIG. 4 b illustrates another variant embodiment of the invention.

In this variant, the link between the offline console 400 and the module20 is made by a wireless link.

This wireless link of the device in FIG. 4 b effectively transfers dataand signals mentioned hereinabove, by means of wireless transmission.

Such means can for example comprise a radio frequency transmitter andreceiver. This can for example be a link of BlueTooth type (registeredtrade mark).

In the case of the variant illustrated in FIG. 4 b, the ventilator ofthe module 20 is associated with a small electric battery which is alsointegrated into the module.

The other characteristics of the device of FIG. 4 b are similar to thoseof the device of FIG. 4 a.

FIG. 5 illustrates another mode of realization of the invention, whichcorresponds to an alternative embodiment.

In this alternative, the module 20 is not fixed directly on the mask 420of the patient. Instead of this, the module 20 is mounted on the console400, or in this console.

In this case, a conduit 110′ still connects the console to the mask ofthe patient, to bring it the respiratory gas which it needs.

This alternative embodiment does not offer all the advantages mentionedhereinabove with reference to the devices of FIGS. 4 a and 4 b, in whichthe module 20 is directly implanted onto the mask of the patient.

But the alternative of FIG. 5 all the same allows simple, rapid and easydisassembly of the ventilator, for cleaning purposes, for example.

And in this case also, the ventilator is an axial ventilator, of thetype illustrated in FIG. 3 a.

It is specified that this type of axial ventilator, apart from the factthat it effectively reduces the space requirement associated with themodule 20, also offers an advantage in terms of operation.

In this respect, it is firstly recalled that breathing assistancedevices can be tracked under flow, or pressure.

In flow tracking, the operation of the ventilator is controlledessentially as a function of the signals coming from a flow sensor ofthe respiratory gas.

This type of tracking corresponds to a so-called volumetric mode of thedevice.

It is also possible to track the device in barometric mode.

In this case, the control signals destined for the ventilator are workedout essentially as a function of the signals coming from the pressuresensor of the respiratory gas.

Such barometric tracking is often adopted to ventilate patientsafflicted with light pathologies (especially patients suffering fromsleep apnoea).

And the applicant has ascertained that a ventilator of axial type wasmore capable than a ventilator of centrifugal type in keeping track ofthe device under pressure.

In effect, such an axial ventilator is particularly well adapted togenerate a flux of respiratory gas with:

relatively low pressures (whereof the value is less than around 25 mb),

with an increased rate (typically having a value greater than around 150l/min).

And this type of pressure and flow values is currently associated withmodes of operation in BPAP or in CPAP, which correspond to operatingmodes of the invention.

It is also specified that using an axial ventilator as a source ofpressurized gas can help boost the safety of the device.

In effect, in the case of a power cut depriving the source ofpressurized gas of electrical power, it will be much easier for thepatient to continue to breathe <<through>> an axial ventilator than<<through>> any other type of source of pressurized gas.

Another advantage still of a source of pressurized gas in the form of anaxial ventilator is that the noise associated with operating such asource is diminished. The comfort of use of the device isincreased—especially within the scope of treating sleep apnoea.

In all the cases in point, the device according to the present inventioncan be a device of type BPAP or CPAP.

Although the invention herein has been described with reference toparticular embodiments, it is to be understood that these embodimentsare merely illustrative of the principles and applications of thepresent invention. It is therefore to be understood that numerousmodifications may be made to the illustrative embodiments and that otherarrangements may be devised without departing from the spirit and scopeof the present invention as defined by the appended claims.

1. A breathing assistance apparatus for a patient, comprising: (a) afirst module including: a source of respiratory pressurized gas, the gassource comprising a ventilator having an inlet rotor and a motor; abreathing connection for allowing the patient to directly receive thepressurized gas; at least one sensor for acquiring a parameterrepresentative of the operation of the device; and a battery with energyfor powering operations of said first module; (b) a second moduleincluding a central control unit for controlling operation of the firstmodule to generate airway pressure ventilation based on information fromsaid at least one sensor; and (c) a wireless link between the firstmodule and the second module, the link enabling said energy to beconveyed from the second module to the first module.
 2. The apparatus ofclaim 1 wherein the at least one sensor comprises a pressure transducer.3. The apparatus of claim 1 wherein the at least one sensor comprises aflow sensor.
 4. The apparatus of claim 1 wherein the breathingconnection of the first module comprises a mask.
 5. The apparatus ofclaim 1 wherein each of said first module and said second module includea radio frequency transmitter and receiver for transmission of data ofthe sensor and control signals for the motor between the first moduleand the second module.
 6. The apparatus of claim 5, wherein thetransmitted control signals to the ventilator control a delivery ofairway pressure ventilation in a BPAP mode.
 7. The apparatus of claim 5,wherein the control signals to the ventilator control a delivery ofairway pressure ventilation in a CPAP mode.
 8. The apparatus of claim 1wherein said first module comprises a removable component beingremovably connectable with the breathing connection, said removablecomponent including first and second parts, the ventilator beingintegrated into the first part, and the at least one sensor beingcontained in the second part.
 9. The apparatus of claim 1, wherein theventilator is an axial ventilator.
 10. The apparatus of claim 7, whereinthe rotor of the axial ventilator comprises a single stage.
 11. Theapparatus of claim 8, wherein the ventilator of the first module isconfigured to output breathable gas in a substantially paralleldirectional flow to the input of the breathable gas to the ventilator.12. A method for providing breathing assistance for a patient,comprising: (a) providing pressurized breathable gas to a patient with afirst module, the first module including: a source of respiratorypressurized gas, the gas source comprising a ventilator having an inletrotor and a motor; a breathing connection for allowing the patient todirectly receive the pressurized gas; at least one sensor for acquiringa parameter representative of the operation of the device; and a batteryenergy source for powering operations of said first module; (b)controlling the first module with a second module, the second moduleincluding a central control unit for controlling operation of the firstmodule to generate airway pressure ventilation based on information fromsaid at least one sensor; and (c) energizing the first module with thesecond module by a wireless link between the first module and the secondmodule, the link enabling said energy to be conveyed from the secondmodule to the first module.
 13. The method of claim 12 wherein the atleast one sensor comprises a pressure transducer.
 14. The method ofclaim 12 wherein the at least one sensor comprises a flow sensor. 15.The method of claim 12 wherein the breathing connection of the firstmodule comprises a mask.
 16. The method of claim 12 wherein each of saidfirst module and said second module include a radio frequencytransmitter and receiver for transmission of data of the sensor andcontrol signals for the motor between the first module and the secondmodule.
 17. The method of claim 16, wherein the transmitted controlsignals to the ventilator control a delivery of airway pressureventilation in a BPAP mode.
 18. The method of claim 16, wherein thecontrol signals to the ventilator control a delivery of airway pressureventilation in a CPAP mode.
 19. The method of claim 12 wherein saidfirst module comprises a removable component being removably connectablewith the breathing connection, said removable component including firstand second parts, the ventilator being integrated into the first part,and the at least one sensor being contained in the second part.
 20. Themethod of claim 12, wherein the ventilator is an axial ventilator. 21.The method of claim 20, wherein the rotor of the axial ventilatorcomprises a single stage.
 22. The method of claim 21, wherein theventilator of the first module is configured to output breathable gas ina substantially parallel directional flow to the input of the breathablegas to the ventilator.